EP1993658B1 - Conducteur medical implantable et procede de fabrication de ce conducteur - Google Patents

Conducteur medical implantable et procede de fabrication de ce conducteur Download PDF

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Publication number
EP1993658B1
EP1993658B1 EP06716962A EP06716962A EP1993658B1 EP 1993658 B1 EP1993658 B1 EP 1993658B1 EP 06716962 A EP06716962 A EP 06716962A EP 06716962 A EP06716962 A EP 06716962A EP 1993658 B1 EP1993658 B1 EP 1993658B1
Authority
EP
European Patent Office
Prior art keywords
helix
protrusions
tissue
electrically
conducting
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
Application number
EP06716962A
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German (de)
English (en)
Other versions
EP1993658A1 (fr
Inventor
Kenneth Dahlberg
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
St Jude Medical AB
Original Assignee
St Jude Medical AB
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by St Jude Medical AB filed Critical St Jude Medical AB
Publication of EP1993658A1 publication Critical patent/EP1993658A1/fr
Application granted granted Critical
Publication of EP1993658B1 publication Critical patent/EP1993658B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/04—Electrodes
    • A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/04—Electrodes
    • A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A61N1/056—Transvascular endocardial electrode systems
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T29/00—Metal working
    • Y10T29/49—Method of mechanical manufacture
    • Y10T29/49002—Electrical device making
    • Y10T29/49117—Conductor or circuit manufacturing

Definitions

  • the invention relates to a medical implantable lead being adapted to be inserted into a human or animal body and attached, with its distal end, to tissue inside the body, comprising a rotatable helix in the distal end which can be screwed into the tissue, the helix being adapted to serve as an attachment of the lead to the tissue as well as to serve as a conductor for conducting of electrical signals to the tissue through electrical conducting surfaces on the helix, wherein the surfaces of the helix being partly insulated to restrict the conducting of signals between the helix and the tissue to desirable regions.
  • the invention also relates to a method for manufacturing of a helix for a medical implantable lead.
  • a medical implantable lead of the above kind may be used for different purposes. E.g. connected to a pacemaker for monitoring and pacing the activity of a human heart, as a nerve stimulator or connected to a diagnostic device for monitoring and stimulating the activity of an arbitrary organ in a human or animal body.
  • Such a diagnostic and therapeutic device is often implanted into the body to perform its function during a long time.
  • the electrical power source for power supply to the lead is in form of at least one battery positioned in the device.
  • the current drain from the lead has a great influence on the overall power consumption and if the transition impedance from the helix in the lead to body tissue is increased, the current drain will be reduced.
  • One way to achieve this is to restrict the electrically conductive surfaces on the helix by applying an insulating layer on parts of the surface thereof.
  • US 5476502 discloses a defibrillation electrode in the shape of a helix that, although a part of the inside of the helix is provided with an insulating layer, is designed to have a conducting surface that is as large as possible and hence with a low impedance.
  • the object of the present invention is to provide an improved medical implantable lead. More precisely, it is an object of the invention to further restrict the current drain from medical implantable leads in comparison to leads known in the art, and provide a medical implantable lead which utilizes the current emitted from the helix in a more effective way. At least this object is achieved by a medical implantable lead according to claim 1.
  • the invention also relates to a method for manufacturing a medical implantable lead of the above kind.
  • the object of the method is to manufacture the lead in an effective, reliable and cost effective way. At least this object is achieved by a method according to claim 9.
  • the present invention is based on the insight that the above object may be achieved by a medical implantable lead having a helix, of which at least the surfaces facing inwards toward an inner bore of the helix are electrically insulated.
  • the reason for this is that it has been found, according to the invention, that any current emitted from the inward facing surfaces of the helix has no or only an insignificant effect on the tissue.
  • the electrically conductive regions are formed with alternating conducting surfaces as well as insulated surfaces in a desired pattern. In this way the current emission will be concentrated to the limited electrically conductive surfaces.
  • the conductive pattern may be arbitrary formed.
  • the invention may be realized in many different ways.
  • the surfaces of the helix having an arbitrary cross sectional form, which in a cross section of the helix is facing inwards toward an inner bore of the helix and positioned within lines, each constituting a normal to a tangent of the helix surface and touching an inner surface of an adjacent coil of the helix, are electrically insulated.
  • the inner and lateral surfaces of the helix having an arbitrary cross sectional form, which in a cross section of the helix is facing inwards toward an inner bore of the helix and laterally toward adjacent coils of the helix and positioned within lines, each constituting a normal to a tangent of the inner surface and touching an outer surface of an adjacent coil of the helix, are electrically insulated. Consequently, according to this embodiment, also the surfaces of the helix facing adjacent coils of the helix are electrically insulated.
  • the inner surfaces and lateral surfaces of the helix which, in a cross section of the helix, is facing inwards toward a bore of the helix and toward adjacent coils of the helix, respectively, are electrically insulated. Consequently, only the outward facing surfaces of the helix are provided with electrically conducting surfaces.
  • not all of the areas of the outward facing surfaces of the helix are electrically conductive. Instead the outward facing surfaces of the helix are provided with electrically insulated regions as well as conductive regions in a desirable configuration. E.g. when using a lead where the helix is extendable out from the bore of a tubular or sleeve formed tip, usually not the entire helix is extendable. Instead a part of the helix will remain inside the sleeve and it is unfavourably that any surfaces of that part are made electrically conducting. Therefore, in one embodiment, at least this part of the helix is completely insulated.
  • the tissue to be stimulated or monitored often has an external mucous membrane which is electrically inactive and therefore preferably also a part of the helix outside the tubular tip, having a length of at least 0,3 mm and preferably between 0,3-1,0 mm, is completely insulated.
  • an external mucous membrane which is electrically inactive and therefore preferably also a part of the helix outside the tubular tip, having a length of at least 0,3 mm and preferably between 0,3-1,0 mm, is completely insulated.
  • a distal end portion of between 0,3-1,0 mm of the helix is completely insulated in one embodiment.
  • the pattern of electrically conductive surfaces is in form of protrusions, which project from the surface and which preferably are formed with sharp edges or points. In this way the current emission will be advantageously locally concentrated to the edges and points.
  • the protrusions are pyramid shaped, having three or more essentially plane surfaces as well as the same number of edges and one tip, or shaped as a truncated pyramid or conical shaped with no edges but one tip.
  • the protrusions may preferably have an area of 0,005 mm 2 to 0,1 mm 2 , typically about 0,04 mm 2 , and a centre to centre spacing of 0,1 mm to 0,5 mm, preferably about 0,3 mm, corresponding to the length of one to three muscle cells in the heart. In this way the possibility for each protrusion to stimulate or monitor at least one muscle cell is enhanced, although the possibility for two or more adjacent protrusions to stimulate the same muscle cell is eliminated.
  • a helix according to the invention can be built up and manufactured in many different ways.
  • the cross sectional shape may be for example circular or rectangular.
  • a straight metal wire of e.g. tantalum, having a circular cross section, which is flattened to a somewhat rectangular shape and processed to form protrusions on one side or section of its circumference.
  • the wire is provided with an electrically insulating layer, e.g. of non-conductive diamondlike carbon (DLC), which is coated over its entire external surface. Subsequently, the insulating layer is removed from the protrusion in one or more desirable regions of the wire.
  • DLC non-conductive diamondlike carbon
  • the wire may be rolled between two rollers of which one has a comparably soft layer into which the protrusions will be pressed during the rolling such that the insulating layer will be abraded from the protrusions.
  • the layer is made of DLC another way might be to remove the layer over the protrusions with a laser beam, which would have the advantage that the removed carbon would be turned into carbondioxide with no other residues.
  • the protrusions may then be provided with a layer of tantalum oxide (Ta 2 O 5) or another material with corresponding properties, which will yield a highly capacitive transition zone combined with a high faradic resistance. After this, the wire will be formed into a helix, having the protrusions facing outwards, and cut into pieces of suitable lengths.
  • the structural body of the helix of an electrically insulating material, e.g. carbon fibre reinforced plastics, which is provided with an electrically conducting lead, e.g. a metal wire positioned inside the helix.
  • an electrically conducting lead e.g. a metal wire positioned inside the helix.
  • the lead hereinafter described is provided with a tubular distal end, into which a helix may be retracted in an inactive state, and extendable to an active state by screw rotating the helix in relation to the tubular end.
  • the helix also can be fixed in relation to the rest of the lead, wherein screw rotating of the helix into the tissue is accomplished by rotating the entire lead.
  • fig 1 In a perspective view, a distal portion of an electrical lead for a pacemaker application.
  • the lead is tubular or sleeve formed in its distal end, defining a bore 1 into and out from which a helix 2 is retractable and extendable by screw rotating it by means of some suitable means known in the art, however not shown in the drawings.
  • the inward facing surfaces of the circumference of the helix are electrically insulated.
  • the outward facing surfaces of the helix may optionally be electrically conducting over a continuous area and/or in restricted areas and/or in spots in an arbitrary pattern.
  • figs 2 and 3 are illustrated two alternative definitions of the surfaces of a helix wire which are adapted to be electrically conductive, or provided with electrically conducting spots in a desired pattern, and electrically insulated, respectively.
  • the cross sectional shape of the wire may be arbitrary although it is shown as being circular in the drawings.
  • a first definition illustrated in fig 2 , the surfaces of the helix which, in a cross section of the helix wire, are facing inwards toward a bore of the helix and positioned within lines 3 constituting a normal to a tangent 4 of the inner surface and touching an inner surface of adjacent coils of the helix, are electrically insulated.
  • the surfaces within the angle segment ⁇ 1 are electrically conducting, either completely or partly in a desired pattern, wherein the surfaces 7 within the angle segment ⁇ 1 are electrically insulating.
  • the inner surfaces of the helix which, in a cross section of the helix, are facing inwards and laterally toward the bore as well as adjacent coils of the helix and positioned within lines 3 constituting a normal to a tangent 4 of the inner surface and touching an outer surface of adjacent coils of the helix, are electrically insulated.
  • the surfaces within the angle segment ⁇ 2 are electrically conducting, either completely or partly in a desired pattern, wherein the surfaces 7 within the angle segment ⁇ 2 are electrically insulating.
  • the outward facing surfaces of the helix may be divided into regions being partly or completely electrically conducting and regions being completely electrically insulated. This is illustrated in fig 4 where a distal portion a, including a tip 5 of the helix 2, is completely electrically insulated. An intermediate portion b of the helix, on the other hand, is provided with electrically conducting spots 6 and surrounding insulated surfaces 7 in a desired pattern. Also a proximal portion c of the helix is electrically insulated. This portion of the helix is, when mounted to the lead, located inside the bore 1 of the lead and attached to a rotatable shaft. Also a small portion of the helix being located immediately outside of the bore in an extended state of the helix, is in a preferred embodiment completely insulated. This latter portion may be at least 0,3 mm and preferably between 0,3 to 1,0 mm.
  • the one or more electrically conducting regions b of the outward facing surfaces of the helix 2 are in a preferred embodiment not electrically conducting over the entire area of that region. Instead, the electrically conducting region is provided with electrically conducting spots 6 surrounded by electrically insulated surfaces 7 in a desired pattern. In fig 5 , one embodiment of such a partial conducting region is depicted in a cross section.
  • the electrically conducting spots are protrusions having pyramidal shape with a square base, which protrude from an electrically conducting base material 8 of the helix through an electrically insulating layer 7 surrounding the helix cross section.

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  • Health & Medical Sciences (AREA)
  • Cardiology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Electrotherapy Devices (AREA)
  • Prostheses (AREA)
  • Surgical Instruments (AREA)

Claims (7)

  1. Conducteur médical implantable étant adapté pour être inséré dans un corps humain ou animal et lié, avec son extrémité distale, à un tissu à l'intérieur du corps, comprenant une hélice rotative (2) dans l'extrémité distale qui peut être vissée dans le tissu, l'hélice étant adaptée pour servir de liaison du conducteur au tissu ainsi que pour servir de conducteur pour la conduction de signaux électriques vers le tissu à travers des surfaces conductrices électriques (6) sur l'hélice, dans lequel les surfaces de l'hélice sont partiellement isolées (7) pour limiter la conduction de signaux entre l'hélice et le tissu à des régions souhaitables (b), dans lequel au moins les surfaces de l'hélice (2) qui, dans une coupe transversale de l'hélice, est positionnée à l'intérieur de lignes (3) constituant une normale à une tangente (4) de la surface interne et touchant une surface interne d'enroulements adjacents de l'hélice, sont pourvues d'une couche isolante (7), caractérisé en ce que les régions électriquement conductrices (b) des surfaces externes de l'hélice (2) comprennent des protubérances électriquement conductrices (6) saillant des surfaces isolées (7).
  2. Conducteur médical implantable selon la revendication 1, caractérisé en ce que les surfaces internes de l'hélice (2) qui, dans une coupe transversale de l'hélice, est positionnée à l'intérieur de lignes (3) constituant une normale à une tangente (4) de la surface interne et touchant une surface externe d'enroulements adjacents de l'hélice, sont pourvues d'une couche isolante (7).
  3. Conducteur médical implantable selon la revendication 2, caractérisé en ce que l'hélice (2) est formée d'un fil présentant une coupe transversale essentiellement rectangulaire, dans lequel un côté du fil tourné vers l'extérieur est pourvu des protubérances électriquement conductrices (6) saillant des surfaces isolées (7) tandis que les surfaces sur les côtés restants sont électriquement isolées (7).
  4. Conducteur médical implantable selon l'une quelconque des revendications 1 à 3,
    caractérisé en ce que les protubérances (6) comprennent des bords ou pointes aigus.
  5. Conducteur médical implantable selon l'une quelconque des revendications 1 à 4,
    caractérisé en ce que les protubérances (6) présentent des bouts pointus.
  6. Conducteur médical implantable selon l'une quelconque des revendications 1 à 5,
    caractérisé en ce que les protubérances (6) présentent la forme de pyramides ou de pyramides tronquées.
  7. Procédé de fabrication d'une hélice (2) pour un conducteur médical implantable, du type adapté pour lier le conducteur à un tissu corporel et pour conduire des signaux électriques vers le tissu, l'hélice étant pourvue de surfaces (6) étant électriquement conductrices ainsi que de surfaces (7) étant électriquement isolées, comprenant l'étape consistant à :
    fournir un fil de matériau électriquement conducteur,
    caractérisée par les étapes consistant à :
    former des protubérances (6) dans des zones de surface souhaitées du fil ;
    revêtir le fil, y compris les protubérances, d'une couche électriquement isolante (7) ; et
    découvrir les protubérances de la couche isolante couvrante dans des régions souhaitées.
EP06716962A 2006-03-02 2006-03-02 Conducteur medical implantable et procede de fabrication de ce conducteur Expired - Lifetime EP1993658B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/SE2006/000275 WO2007100277A1 (fr) 2006-03-02 2006-03-02 Conducteur medical implantable et procede de fabrication de ce conducteur

Publications (2)

Publication Number Publication Date
EP1993658A1 EP1993658A1 (fr) 2008-11-26
EP1993658B1 true EP1993658B1 (fr) 2009-10-07

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US (1) US8099177B2 (fr)
EP (1) EP1993658B1 (fr)
AT (1) ATE444776T1 (fr)
DE (1) DE602006009712D1 (fr)
WO (1) WO2007100277A1 (fr)

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US20090171425A1 (en) 2009-07-02
ATE444776T1 (de) 2009-10-15
EP1993658A1 (fr) 2008-11-26
US8099177B2 (en) 2012-01-17
WO2007100277A1 (fr) 2007-09-07
DE602006009712D1 (de) 2009-11-19

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